Oximeter ambient light cancellation

ABSTRACT

A pulse oximeter method and apparatus which provides (1) a notch filter at a distance between a modulation frequency and a common multiple of commonly used power line frequencies (50, 60, 100 and 120) and also (2) a demodulation frequency greater than a highest pulse rate of a person and lower than any harmonic of 50, 60, 100 or 120 Hz, to filter ambient light interference, while choosing an optimum demodulation frequency that avoids interference from the notch filter or from harmonics of the line interference. Also, ambient light for any low frequency interference, such as power line interference, is measured both before and after each of the light emitter wavelengths and the average of the ambient light is then subtracted from the detected signal.

CROSS-REFERENCE TO RELATED APPLICATION

This application is a continuation of application Ser. No. 12/172,981,filed Jul. 14, 2008, in the name of Ethan Petersen, now U.S. Pat. No.8,315,684 which granted on Nov. 20, 2012 and assigned to Covidien LP,which is a continuation of application Ser. No. 11/495,415, filed Jul.28, 2006, in the name of Ethan Petersen, now U.S. Pat. No. 7,400,919which granted on Jul. 15, 2008 and assigned to Covidien LP, which is adivisional of application Ser. No. 10/787,854, filed Feb. 25, 2004, inthe name of Ethan Petersen, now U.S. Pat. No. 7,190,985, which grantedon Mar. 13, 2007 and assigned to Covidien LP, which are incorporatedherein by reference in their entirety.

BACKGROUND OF THE INVENTION

The present invention relates to oximeters, and in particular totechniques for ambient light cancellation in pulse oximeters.

Pulse oximetry is typically used to measure various blood flowcharacteristics including, but not limited to, the blood-oxygensaturation of hemoglobin in arterial blood, the volume of individualblood pulsations supplying the tissue, and the rate of blood pulsationscorresponding to each heartbeat of a patient. Measurement of thesecharacteristics has been accomplished by use of a non-invasive sensorwhich scatters light through a portion of the patient's tissue whereblood perfuses the tissue, and photoelectrically senses the absorptionof light in such tissue. The amount of light absorbed is then used tocalculate the amount of blood constituent being measured.

The light scattered through the tissue is selected to be of one or morewavelengths that are absorbed by the blood in an amount representativeof the amount of the blood constituent present in the blood. The amountof transmitted light scattered through the tissue will vary inaccordance with the changing amount of blood constituent in the tissueand the related light absorption. For measuring blood oxygen level, suchsensors have typically been provided with a light source that is adaptedto generate light of at least two different wavelengths, and withphotodetectors sensitive to both of those wavelengths, in accordancewith known techniques for measuring blood oxygen saturation.

Known non-invasive sensors include devices that are secured to a portionof the body, such as a finger, an ear or the scalp. In animals andhumans, the tissue of these body portions is perfused with blood and thetissue surface is readily accessible to the sensor.

One problem with oximeter measurements is that in addition to receivingthe light that was directed at the tissue, ambient light is alsodetected by the photodetector. Attempts can be made to block out ambientlight, but some amount of ambient light will typically be detected. Oneparticular concern is the light at the power line frequency offluorescent or other lights, which is 60 Hz in the United States and 50Hz in Europe and other countries.

Since a single photodetector is typically used, the light of differentwavelengths, such as red and infrared, is time multiplexed. The detectedsignal must be demultiplexed. The demultiplexing frequency must be highenough so that it is much larger than the pulse rate. However, choosinga demultiplexing frequency is also impacted by the ambient lightinterference. One issue is the aliasing of harmonics of the AC powerline frequency. U.S. Pat. No. 5,713,355 discusses a technique ofaltering the demultiplexing frequency depending upon the amount ofambient interference detected at each frequency.

U.S. Pat. No. 5,885,213 discusses subtracting a dark signal (detectedambient light) from the detected light signal. This is accomplished byleaving both the red and infrared light emitters off, in between turningthem on, so that a “dark” signal supposedly composed of the ambientlight present can be detected. This can then be subtracted from thedesired signal. Other examples of patents dealing with the ambient lightissue are U.S. Pat. Nos. 6,385,471, 5,846,190 and 4,781,195.

U.S. Pat. No. 6,449,501 discusses using a notch filter to filter outline frequency. However, the sampling rate is described as being set totwice the fundamental frequency of the power line interference, leavinghigher harmonics of the power line interference as a problem, and it isunclear how the interference can be filtered without filtering themodulation frequency. Another example of a notch filter being used isset forth in U.S. Pat. No. 4,802,486, which uses a notch filter for theEKG signal.

BRIEF SUMMARY OF THE INVENTION

The present invention provides a pulse oximeter method and apparatuswhich provides (1) a notch filter at a distance between a demodulationfrequency and a common multiple of commonly used power line frequencies(50, 60, 100, and 120) and also (2) a demodulation frequency greaterthan a highest pulse rate of a person and lower than any harmonic of 50,60, 100, or 120 Hz. The invention thus allows the filtering of asignificant source of ambient light interference, while choosing anoptimum demodulation frequency that avoids interference from the notchfilter or from harmonics of the power line interference.

In one embodiment, the common multiple is 1200, with the demodulationfrequency being between 5 and 20 Hz away from 1200, preferablyapproximately 1211 in one embodiment.

In another aspect of the invention, dark signals, or ambient light, aremeasured both before and after each of the light emitter wavelengths(red and infrared in one embodiment). Instead of simply subtracting oneof the dark levels, the two dark levels are averaged and then subtractedfrom the detected signal. This compensates for a variation in ambientlight during the detected signal, reducing the effect of power lineinterference or any other low frequency interference.

In a another aspect of the present invention, digital filtering anddecimation are done in the digital domain. When there is a change in again setting on the front end hardware, or in the LED power, the filtersare preloaded to put values in their memory to correspond to an estimateof the settled value of the output at the new gain or power settings.This preloading speeds up when valid data will be available at theoutput of the filter.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a block diagram of an oximeter incorporating the presentinvention.

FIG. 2 is a block diagram of a portion of the digital manipulations inone embodiment of the invention, including a notch filter.

FIG. 3 is a diagram illustrating the multiple dark levels that areaveraged in an embodiment of the invention.

FIG. 4 is a diagram illustrating the preloading of the digital filterand decimator according to an embodiment of the present invention.

DETAILED DESCRIPTION OF THE INVENTION

Overall System

FIG. 1 illustrates an embodiment of an oximetry system incorporating thepresent invention. A sensor 10 includes red and infrared LEDs and aphotodetector. These are connected by a cable 12 to a board 14. LEDdrive current is provided by an LED drive interface 16. The receivedphotocurrent from the sensor is provided to an I-V interface 18. The IRand red voltages are then provided to a sigma-delta interface 20incorporating the present invention. The output of sigma-delta interface20 is provided to a microcontroller 22. Microcontroller 22 includesflash memory for a program, and EEPROM memory for data. The oximeteralso includes a microprocessor chip 24 connected to a flash memory 26.Finally, a clock 28 is used and an interface 30 to a digital calibrationin the sensor 10 is provided. A separate host 32 receives the processedinformation, as well as receiving an analog signal on a line 34 forproviding an analog display.

Notch Filter

FIG. 2 shows an analog-to-digital converter 40 which provides a digitalsignal to be manipulated by microcontroller 22 of FIG. 1. Themicroprocessor would include a demodulator 42, four stages offilter/decimators 44, a low pass filter with a notch 46, as well asother blocks for digital manipulation of the signals and calculation ofoxygen saturation as is well known in the art. Only the red channel isshown after the demodulation, but a similar channel is used for the IRsignal.

Notch filter 46 deals with power line interference which, in the UnitedStates, comes from lights which operate on 60 Hz or 120 Hz, dependingupon the power requirements. Europe and other areas use 50 Hz and 100Hz. A common multiple of 50, 60, 100, and 120 Hz is 1200 Hz. Themodulation bandwidth is chosen to be higher than the highest possiblehuman pulse rate, preferably higher than 5 Hz. At the same time, it ischosen to be lower than any harmonic of the power line interferencesignals. Twenty hertz is chosen as a desirable upper limit because asecond harmonic of 2450 will alias in at 2025 Hz. In one embodiment, themodulation frequency chosen is 1211.23 Hz. This is 11.23 Hz distant from1200 Hz. (within a range of 5-20 Hz). Accordingly, in a preferredembodiment, a zero is provided in the notch filter at 11.23 Hz. The lowpass filter with notch (46), in one embodiment, is an 8 pole Besselfilter with a notch at 11.25 Hz.

The present invention thus provides an effective means of eliminatinginterference from power line interference, such as the ripple onfluorescent lights which can alias onto the detected signal. Althoughanti-aliasing filters have been provided in hardware before ademodulator, it is difficult to make these effective, and thus therewill be some residual line interference in the detected signal to bedealt with in the digital domain.

Averaging Ambient Dark Levels to Reduce Low Frequency Interference

FIG. 3 illustrates another aspect of the present invention, reducingambient interference by averaging the ambient dark levels before andafter a sampling period to account for low frequency interference frompower lines or other sources. FIG. 3 shows a signal at a sampling rateof 2400. The upward sloping line in FIG. 3 is due to 60 Hz power lineinterference. It is desirable to eliminate the effect of this upwardslope (which will be downward on other parts of the 60 Hz (or 50 Hz,etc.) signal.

FIG. 3 shows a detected signal during different periods of modulation.The detected signal level is illustrated by a line 50. During a firstdark period 52, neither the red nor IR LED are on, allowing a samplingof the dark, or ambient, light. After this sampling, during a timeperiod 54, the red LED is turned on, with signal 50 rising during thisperiod as the red LED comes on to its full intensity. During the timeperiod 56, the detected signal corresponds to the red LED being on.

After the red LED is turned off and the signal decays during a period58, a second dark period 60 is sampled.

Subsequently, the IR LED is turned on during a period 62, and sampledduring a period 64. It is turned off and the signal decays during aperiod 66, with a third dark sample being taken during a period 68. Thethird dark sample also corresponds to the first dark period 52, as theprocess repeats itself.

As can be seen from FIG. 3, if only one of the dark levels is used, aninaccurate ambient level may be measured if the ambient level isvarying, such as due to low frequency interference. By averaging thedark periods before and after the sampling period for a particularwavelength, a more accurate measurement of the ambient dark level signalis obtained. For example, the ambient interference during the redmodulation period 56 is determined by measuring the dark 1 signal duringperiod 52 and the dark 2 signal during period 60 and averaging thesesignals. Similarly, for the infrared modulation period 64, the dark 2signal during period 60 and the dark 3 signal during period 68 areaveraged and subtracted from the detected IR signal to eliminate theambient interference. All of these calculations are done in the digitaldomain by microcontroller 22 of FIG. 1.

Preloading Decimation and Bessel Filters

FIG. 4 illustrates another aspect of the present invention where filtersand software are preloaded. Before the analog input signal is processedthrough the sigma-delta modulator and multi-bit analog digitalconverter, it is typically amplified in a hardware amplifier 84. Afterprocessing by the sigma-delta modulator 86 and conversion into digitaldomain, it is decimated to reduce the sample rate by a decimator 88 andfiltered by a Bessel filter 88. A controller 92 pre-loads the memoriesof the Bessel filter and decimator with an estimate of what the settledvalue of the output would be. This will significantly reduce thesettling time of the filter after a step change in its input. Such astep change in the input can occur from a change in the gain settings ofthe amplifier 84. Alternately, a step change can be the result of achange in the particular LED being activated, the power of the LED, orother gain settings of the front end hardware. Since the controller 92would be activating such changes, it will have the knowledge of when topre-load the filter and decimator with the appropriate values.

Although these are shown as blocks in FIG. 4, it is understood that inthe preferred embodiment this is done by a software program whichfunctions as controller 92, filter 88 and decimator 90. This preloadingof the filter and decimator provides that valid data is available soonerby shortening the settling time.

As will be understood by those skilled in the art, the present inventionmay be embodied in other specific forms without departing from theessential characteristics thereof. For example, more than two differentwavelengths of light could be used. Alternately, a differentdemodulation frequency could be chosen. In addition, the notch filteringcan be done either before or after other digital processing of thedetected signal. Accordingly, the foregoing description is intended tobe illustrative, but not limiting, of the scope of the invention whichis set forth in the following claims.

What is claimed is:
 1. A method for operating a pulse oximetry system,comprising: alternately generating light with a sensor at twowavelengths using a modulation frequency that is a predetermineddistance from a common multiple of 50, 60, 100, and 120, where thepredetermined distance is greater than a highest pulse rate of a personand lower than a distance of any harmonic of 50, 60, 100, or 120;receiving an analog sensor signal from the sensor that corresponds toreceived light; amplifying the analog sensor signal to provide anamplified analog sensor signal; modulating the amplified analog sensorsignal with a sigma-delta modulator to provide a modulated signal;converting the modulated signal into a digital signal with a multiplebit analog-to-digital converter; decimating the digital signal with adecimator to provide a decimated signal; filtering the decimated signalwith a digital filter to provide a filtered signal; and preloading thedecimator and digital filter with an estimate of a settled output value.2. The method of claim 1 wherein processing the received light signalcomprises digitizing the processed signal.
 3. The method of claim 1wherein the common multiple comprises
 1200. 4. The method of claim 1wherein the predetermined distance is between 5 and 20 hertz.
 5. Themethod of claim 1 wherein the predetermined distance is approximately 11hertz.
 6. The method of claim 1 comprising determining a physiologicalparameter based at least in part on the filtered signal.
 7. The method,as set forth in claim 1, wherein amplifying comprises using a hardwareamplifier.
 8. The method, as set forth in claim 1, wherein filteringcomprises using a Bessel filter.
 9. The method, as set forth in claim 1,wherein preloading comprises using a controller.
 10. A pulse oximetrysystem, comprising: a first processor board, the first processor boardcomprising: an interface for receiving an analog sensor signal; asigma-delta modulator configured to receive the sensor signal and toprovide a modulated signal; an analog-to-digital converter configured toconvert the modulated signal into a digital signal; a decimatorconfigured to receive the digital signal and output a decimated signaloperated on by a digital filter, wherein the first processor boardcomprises a controller is configured to preload the decimator and thedigital filter; a processor configured to receive the decimated signaland provide an output related to a physiological parameter; and a secondprocessor board comprising an interface for receiving the output relatedto the physiological parameter from the first processor board.
 11. Thepulse oximetry system, as set forth in claim 10, wherein the firstprocessor board comprises a hardware amplifier configured to amplify thesensor signal.
 12. The pulse oximetry system, as set forth in claim 10,wherein the controller is configured to preload the decimator and thedigital filter after a step change in the decimated signal.
 13. Thepulse oximetry system, as set forth in claim 10, wherein the controlleris configured to preload the decimator and the digital filter inresponse to a change in a gain setting of the amplifier.
 14. The pulseoximetry system, as set forth in claim 10, wherein the controller isconfigured to preload the decimator and the digital filter in responseto a change in an LED associated with the sensor signal being activated.15. The pulse oximetry system, as set forth in claim 10, wherein thecontroller is configured to preload the decimator and the digital filterin response to a power change in an LED associated with the analogsensor signal.
 16. The pulse oximetry system, as set forth in claim 10,wherein the controller is configured to preload the decimator and thedigital filter in response to the controller changing a setting of theoximeter apparatus.
 17. The pulse oximetry system, as set forth in claim10, wherein first board comprises a processor comprising executableinstructions configured to control light to be alternately driven into atissue site using a modulation frequency to alternate between a firstperiod of time when a first wavelength is being generated, a dark periodof time when no light is being generated, and a second period of timewhen a second wavelength is being generated; estimate a first level ofambient light in a signal received from the tissue site during the firstperiod of time by averaging detected light received during the darkperiods before and after the first period; estimate a second level ofambient light in the signal received from the tissue site during thesecond period of time by averaging detected light received during thedark periods before and after the second period; calculate a total lightsignal by subtracting the first level of ambient light from the signalreceived from the tissue site generated during the first period of timeand subtracting the second level of ambient light from the signalreceived from the tissue site generated during the second period oftime; and calculate at least one patient characteristic based on thetotal light signal.
 18. A pulse oximetry system, comprising: a firstprocessor board, the first processor board comprising: a first interfacefor receiving an analog sensor signal from a sensor; a second interfacefor receiving calibration information from the sensor; a sigma-deltainterface configured to receive the sensor signal and to provide amodulated signal; an analog-to-digital converter configured to convertthe modulated signal into a digital signal; a decimator configured toreceive the digital signal and output a decimated signal operated on bya digital filter, wherein the first processor board comprises acontroller configured to preload the decimator and the digital filter; aprocessor configured to receive the decimated signal and provide ananalog output; and a second processor board comprising a host interfacefor receiving the analog output from the first processor board.
 19. Thepulse oximetry system, as set forth in claim 18, comprising controlcircuitry for providing a display based at least in part on the analogoutput.